Cryoplasty device and method

ABSTRACT

A cryoplasty catheter and method for preventing or slowing reclosure of a lesion following angioplasty. The cryoplasty catheter includes a shaft having proximal and distal ends and a dilatation balloon disposed at the distal end. An intake lumen and exhaust lumen are defined by the shaft to deliver coolant to the balloon and to exhaust or drain coolant from the balloon. The method in accordance with the present invention includes cooling a lesion to aid in remodeling the lesion through dilatation and/or freezing a portion of the lesion adjacent the dilatation balloon to kill cells within the lesion to prevent or retard restenosis.

This is a continuation of application Ser. No. 09/916,147 as filed onJul. 25, 2001 U.S. Pat. No. 6,648,878, which is a continuation ofapplication Ser. No. 09/229,080 as filed on Jan. 12, 1999, now U.S. Pat.No. 6,290,696, which is a divisional of application Ser. No. 08/812,804as filed on Mar. 6, 1997, now U.S. Pat. No. 5,868,735.

FIELD OF THE INVENTION

The present invention pertains generally to the field of angioplastyand, in particular, to a form of angioplasty involving lesion cooling.

BACKGROUND OF THE INVENTION

Conventional angioplasty has been preformed for several decades,prolonging the lives of an ever increasing number of patients.Angioplasty procedures involves the dilatation of a balloon placedacross a lesion in a coronary artery. Dilatation of the balloon in turndilates the lesion, opening the artery for increased blood flow. In somecases, however, the goal of the angioplasty procedure is, in whole or inpart, frustrated by complete or partial reclosure of the artery at thelesion. Two mechanisms are believed to be principally responsible forreclosure of the artery, these are restenosis and recoil. Restenosis isbelieved to be caused by continued growth or regrowth of the smoothmuscle cells associated with the lesion. Recoil is in part a mechanicalprocess involving elastic rebound of the dilated lesion.

Several means have been disclosed for addressing the problem ofrestenosis. These include, among others, radiation treatments to slow orprevent smooth muscle cell proliferation associated with the restenoticprocess. Certain drug therapies have been proposed to prevent or slowrestenosis.

Several means have also been developed to address the issue of recoil.One of the more significant developments in this area has been stents,which can be permanently deployed to mechanically hold open lesions.Although stents have been found to be highly effective, they mayirritate the wall of a artery in which they are implanted. Some believethat this may encourage limited restenosis. Warming of the lesion duringdilatation has also been disclosed to prevent or slow recoil. Warmingthe lesion is believed to soften the lesions such that it may be“remodeled” that is, thinned under low pressure. Heating of the lesion,however, is believed to cause an injury response which may cause somerestenosis.

SUMMARY OF THE INVENTION

The present invention is directed at an apparatus and method forperforming angioplasty and preventing or slowing the post-procedurereclosure of a dilated lesion. The present invention cools the lesion toprevent or slow reclosure by the mechanisms of restenosis or recoil. Acryoplasty catheter is provided to cool the lesion to aid in remodelingthe lesion to prevent or slow recoil. The present invention can also beused to cool the lesion to freeze a portion of the lesion tissue. Thisis believed to kill cells within the lesion which would promoterestenosis.

A preferred embodiment of the cryoplasty catheter in accordance with thepresent invention includes a shaft having proximal and distal ends. Theshaft defines an inflation lumen, coolant intake lumen and exhaust lumentherethrough. Each lumen has a proximal and distal end proximate theproximal and distal ends of the shaft respectively. A dilatation balloonis disposed at the distal end of the shaft and is in fluid communicationwith the inflation lumen. A chamber is disposed within the balloon andis in fluid communication with the intake and exhaust lumens. A sourceof coolant is connected to the proximal end of the shaft in fluidcommunication with the coolant intake lumen.

A thermo-resistive sensor can be disposed on the dilatation balloon tomonitor the temperature of the lesion. A second thermo-resistive sensorcan be disposed on the shaft to provide a control temperature reading.

In another preferred embodiment of the cryoplasty catheter in accordancewith the present invention, the cryoplasty catheter includes a shafthaving proximal and distal ends. The shaft defines an inflation lumenand a drain lumen therethrough. Each lumen has a proximal and a distalend proximate the proximal and distal ends of the shaft respectively. Adilatation balloon is disposed at the distal end of the shaft and is influid communication with the inflation and drain lumens. The cryoplastycatheter also includes a coolant source connected to the proximal end ofthe shaft in fluid communication with the inflation lumen.

This embodiment of the cryoplasty catheter can also include athermo-resistive sensor disposed on the dilatation balloon. As well asthe thermo-resistive sensor disposed on the balloon, a control sensorcan be disposed on the catheter shaft.

A method of performing cryoplasty is also provided which includes thesteps of advancing a cryoplasty catheter across a lesion, inflating thedilatation balloon to dilate the lesion, and delivering coolant to theballoon to cool the lesion. To aid in remodeling, the lesion adjacentthe balloon can be cooled to between 10° C. and −10° C. A portion of thelesion adjacent the balloon can also be frozen to kill cells within thelesion which would otherwise promote restenosis. For enhancedeffectiveness, freezing may be done by flash freezing the tissue for 20to 60 seconds. The cells are preferably frozen at a temperature ofbetween −20° C. and to −40° C.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side view of a cryoplasty catheter in accordance with thepresent invention;

FIG. 2 is a longitudinal cross-sectional view of the distal end of thecryoplasty catheter of FIG. 1;

FIG. 3 is an alternate embodiment of a cryoplasty catheter in accordancewith the present invention; and

FIG. 4 is an alternate embodiment of a cryoplasty catheter in accordancewith the present invention including a surrounding vacuum lumen.

DETAILED DESCRIPTION OF THE INVENTION

Referring now to the drawings wherein like reference numerals refer tolike elements throughout the several views, FIG. 1 is a side view of acryoplasty catheter 10 in accordance with the present invention. Shaft12 has a proximal end and a distal end. A dilatation balloon 14 isdisposed at the distal end of shaft 12. At the proximal end of shaft 12is a manifold 16. Connected to manifold 16 is a pump 18, which can behand pumped for inflating balloon 14. A coolant source 20 is alsoconnected to manifold 16 which, as explained below, provides a supply ofcoolant to balloon 14. Catheter 10 can be provided with athermo-resistive temperature sensor 22 for monitoring the temperature ofa lesion and a thermo-resistive control sensor 24 connected to a monitor26.

FIG. 2 is a longitudinal, cross-sectional view of the distal end ofcatheter 10 including the distal end of shaft 12 and balloon 14. Shaft12 includes an outer tube 28 which defines an inflation lumen 30 influid communication with the interior of balloon 14. A guidewire tube 32defining a guidewire lumen 34 can extend through at least a portion ofshaft 12 to distal of balloon 14. A marker band 36 can be disposed onguidewire tube 32 within balloon 14.

Shaft 12 also includes a coolant intake tube 38 defining a coolant lumen40 in fluid communication with a cooling chamber 42 disposed withinballoon 14. Shaft 12 also includes an exhaust or drain tube 44 whichdefines an exhaust or drain lumen 46 in fluid communication with chamber42. At the distal end of tube 38 is an orifice 48 which preferably has adiameter smaller than that of an orifice 50 at the distal end of tube44. The diameter of orifice 48 could be, for example, about 0.004inches, or larger or smaller depending upon the diameter of orifice 50.

Those skilled in the art will recognize the various materials which canbe advantageously used to make the catheter of the present invention.Those elements not found in conventional angioplasty catheter such ascoolant intake tube 38, chamber 42 and exhaust tube 44 can also be madefrom materials known to those skilled in the art. For example, inlettube 38 can be a hypotube or polyimide tube having an inside diameterof, for example, between 0.001 to 0.020 inches, but preferably between0.002 and 0.010 inches. Exhaust tube 44 can be made from polyimide andhave an inside diameter which is preferably greater than the insidediameter of inlet tube 38. The chamber 42 can be made from polyimide.These materials and dimensions should be viewed as exemplary only, asthose skilled in the art would appreciate the applicability ofalternative dimensions and materials for these elements.

FIG. 3 is a schematic view of another embodiment of a cryoplastycatheter in accordance with the present invention referred to by thenumeral 100. Cryoplasty catheter 100 includes a shaft 112 having aproximal distal end and a distal end. A balloon dilatation balloon 114is disposed at the distal end of shaft 112. Proximate the proximal endof shaft 112 is a pump 118 connected to a coolant source 120 which caninclude refrigeration for controlling the temperature of the coolant.

A guidewire tube 132 defines a guidewire lumen 134 extending through atleast a portion of shaft 112 to the distal end of catheter 100. Acoolant intake/inflation tube 138 having a proximal end and a distal endproximate the proximal and distal ends of shaft 112 defines acoolant/inflation lumen 140. Lumen 140 is in fluid communication withpump 118 proximate its proximal end and balloon 114 proximate its distalend. Shaft 112 also includes an exhaust/drain tube 144 defining a lumen146 and having a proximal and distal end proximate the proximal anddistal ends of shaft 112, respectively. The distal end of lumen 146 isin fluid communication with balloon 114. The proximal end of lumen 146can be in fluid communication with coolant source 120 for recycling ofcoolant, or may be discharged for disposal. Lumen 140 has a distalorifice 148 which is preferably smaller than a distal orifice 150 oflumen 146.

Those skilled in the art will recognize that there are numerousmaterials and methods of manufacture which would be suitable forproduction of catheter 100. Those elements of catheter 100 which are nottypical of angioplasty catheters such as inflation/intake tube 138 andexhaust/drain tube 144 can be made as described above with respect tothe corresponding elements of catheter 10. It should be noted howeverthat tube 138 should be sized appropriately to serve its dual purpose asan inflation tube and coolant intake tube. Additionally, the sizes oftubes 138 and 144, as well as the corresponding elements of catheter 10should be sized to take into account the physical properties of aparticular coolant medium for example, the relative rate of heattransfer to the coolant medium from a lesion.

Another alternate embodiment 212 of a cryoplasty catheter in accordancewith the present invention is shown in FIG. 4. The cryoplasty catheter212 is essentially similar to catheter 12 shown in FIG. 2 except that asheath 260 surrounds tube 28 to define an annular lumen 262 betweensheath 260 and tube 28. Sheath 260 preferably extends from balloon 14proximally to manifold 16. Manifold 16 for this embodiment can includean additional port in fluid communication with lumen 262. Except for theadditional port, lumen 262 should be completely sealed such that avacuum may be maintained within lumen 262 when a vacuum source isapplied to the port. A vacuum can be created in lumen 262 during theprocedure to provide insulation between the coolant and the patient.Sheath 262 can be made from biocompatible materials known to thoseskilled in the art of catheter construction which are sufficiently rigidto prevent lumen 262 from collapsing when a vacuum is created therein.

In use, dilatation balloon 14 of catheter 10 is advanced across a lesionin a conventional manner. Balloon 14 is dilated by forcing fluid intoballoon 14 through inflation lumen 30 with pump 18. Coolant is thenreleased into chamber 42 from a pressurized container or pump (notshown) to cool the adjacent lesion at a rate appropriate to thetreatment goals described in more detail below. The coolant isdischarged from chamber 42 through exhaust or drain lumen 46. The arrowin FIG. 1 proximate manifold 16 shows coolant being discharged to theatmosphere from lumen 46. Coolant may be collected for recycling ordisposal as desired.

In a preferred embodiment of the invention, the inflation fluid is a lowfreezing point liquid such as an ethanol mixture. The coolant is onewhich will provide the appropriate heat transfer characteristicsconsistent with the goals of treatment. Liquid N₂ can be used as ageneral purpose coolant with catheter 10 and is particularly useful whenfreezing of cells within the lesion is desired. When liquid N₂ is usedin catheter 10, it can be transported to chamber 42 in the liquid phasewhere it evaporates at orifice 48 and exits through lumen 46 as a gas.Freon, N₂O gas and CO₂ gas can also be used as coolants. Other coolantscould be used such as cold saline solution which would enter and exitchamber 42 as a liquid, Fluisol or a mixture of saline solution andethanol. It is anticipated that coolants such as saline solution couldbe used with catheter 10 when rapid freezing of cells within a lesion isnot a treatment goal. One skilled in the art would appreciate that othercoolants could be used in a similar manner to achieve one or more of thetreatment goals.

Catheter 100 can be used in a manner similar to catheter 110, exceptthat the coolant must also serve as the inflation fluid. It iscontemplated that in most applications involving catheter 100, a liquidcoolant such as saline solution will be used.

Temperature can be monitored by thermo-resistive sensors 22 and 24either absolutely with pre-calibrated sensors and/or relatively betweensensors 22 and 24. Depending on the treatment goals and temperaturelevel monitored, the flow rate of the coolant into the catheter can beadjusted to raise or lower the temperature of the lesion.

The goal of cryoplasty treatment is to prevent or retard the reclosureof a dilated lesion by preventing or retarding restenosis and/or recoilof the lesion. Cooling the lesion to near 0° C. is believed to changethe characteristics of the lesions in such a way as to enhanceremodeling by low pressure dilatation to prevent or retard recoil of thelesion. Further cooling to freeze the lesion is believed to createapoptosis of the lesion tissue, i.e., killing cells within the lesion.

In a preferred embodiment of the method in accordance with the presentinvention, a cryoplasty catheter such as one described above is used todilate the lesion and slowly cool (for example, over a 1–5 minuteperiod) it to reduce injury to healthy tissue while altering the plaqueto be more susceptible to permanent, mechanical remodeling. Thetemperature of the lesion during dilatation is preferred to be about 0°C. to 20° C. such that the plaque characteristics are significantlyaltered, but normal healthy tissue has been injury preserved.

Alternately or in addition to slow cooling to approximately 0° C. to 20°C. for enhanced remodeling, the lesion can be flash frozen to 0° C. to−40° C. for between 20 to 30 seconds while the balloon is stillinflated. Saline or contrast injections may be utilized pre, or duringfreeze to prevent adjacent blood freezing from creating occlusivethrombus.

The mechanisms of restenosis and recoil are not fully understood. It isbelieved in the case of restenosis, that freezing the thrombus tissueinjures the capillaries that supply the lesion tissue and promote musclecell proliferation. With respect to recoil, it is believed that coolingthe plaque makes it relatively very stiff and crystallized, thus beingmore susceptible to permanent remodeling.

Numerous characteristics and advantages of the invention covered by thisdocument have been set forth in the foregoing description. It will beunderstood, however, that this disclosure is, in many respects, onlyillustrative. Changes may be made in details, particularly in matters ofshape, size, and arrangement of parts without exceeding the scope of theinvention. The inventions's scope is, of course, defined in the languagein which the appended claims are expressed.

1. A cryo-therapy device, comprising: a shaft having a proximal end anda distal end; a cooling chamber disposed at the distal end of the shaftand defining an interior space; a coolant intake tube disposed withinthe shaft, the coolant intake tube having a distal opening in fluidcommunication with the interior space of the cooling chamber andarranged to create a phase change in fluids introduced through thecoolant intake tube, and an exhaust tube disposed within the shaft, theexhaust tube having a distal opening in fluid communication with theinterior space of the cooling chamber, wherein the shaft furthercomprises an inflation lumen in fluid communication with a balloonpositioned around the cooling chamber.
 2. The device in accordance withclaim 1, further comprising an outer sheath disposed over at least aportion of the shaft that defines a vacuum lumen therebetween.
 3. Thedevice in accordance with claim 2, further comprising one or morethermal-resistive sensors disposed proximate the cooling chamber.
 4. Thedevice in accordance with claim 1, further comprising one or morethermal-resistive sensors disposed proximate the cooling chamber.
 5. Thedevice in accordance with claim 4, further comprising an outer sheathdisposed over at least a portion of the shaft that defines a vacuumlumen therebetween.
 6. A method of causing cold-induced tissuetreatment, comprising the steps of: providing a catheter having acooling chamber and a balloon positioned around the chamber; advancingthe cooling chamber near tissue to be treated in a patient'svasculature; and delivering liquid coolant through a coolant intake tubein the catheter and causing a phase change in the coolant to cool thetissue.
 7. The method in accordance with claim 6, further comprising thestep of exhausting gaseous coolant from the cooling chamber through anexhaust tube.
 8. The method in accordance with claim 6, wherein the stepof delivering coolant through the coolant intake tube to the coolingchamber to cool the tissue decreases the temperature of the coolingchamber within the range of about −40° C. to about 20° C.
 9. The methodin accordance with claim 6, further comprising the step of freezing aportion of the tissue.